US20070179577A1 - Medical electrical lead having improved inductance - Google Patents
Medical electrical lead having improved inductance Download PDFInfo
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- US20070179577A1 US20070179577A1 US11/343,655 US34365506A US2007179577A1 US 20070179577 A1 US20070179577 A1 US 20070179577A1 US 34365506 A US34365506 A US 34365506A US 2007179577 A1 US2007179577 A1 US 2007179577A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/362—Heart stimulators
- A61N1/37—Monitoring; Protecting
- A61N1/3718—Monitoring of or protection against external electromagnetic fields or currents
Definitions
- the present invention relates generally to implantable medical device (IMD) leads for delivering active electrodes to various places in a human body, such as the heart.
- IMD implantable medical device
- the present invention relates to lead conductors that are compatible with radio frequency (RF) fields generated by magnetic resonance imaging (MRI).
- RF radio frequency
- Typical leads for use with an IMD such as an implantable cardioverter defibrillation (ICD) device, deliver multiple conductors to the heart for performing pacing, cardioverting, defibrillating, sensing and monitoring functions.
- ICD implantable cardioverter defibrillation
- One or more of these conductors typically comprises a multi-filar cable in which nineteen filars are wrapped around a straight central filar. This type of design yields a cable that has good mechanical properties, including flexibility, weldability and high strength. Strength is particularly important for ensuring adequate electrical and mechanical contact between the conductor and an electrode when an electrode is crimped down on the conductor. For example, a good crimp should produce a 2.5 lbf joint.
- the present invention comprises a strength-enhanced conductor for a medical electrical lead.
- the conductor connects an electrode near a distal end of a medical electrical lead with an implantable medical device connected to a proximal end of the medical electrical lead, and includes a multi-filar coil wrapped around a non-conducting central core.
- the multi-filar coil includes an inductance of approximately 0.5 ⁇ H or greater.
- FIG. 1 shows a medical electrical lead of the present invention for use with an implantable cardioverter defibrillation (ICD) device.
- ICD implantable cardioverter defibrillation
- FIG. 2A shows cross section 2 - 2 of FIG. 1 showing the conductors of the ICD lead.
- FIG. 2B shows a partially cut away perspective view of cross section 2 - 2 of FIG. 1 .
- FIG. 3 shows cross section 3 - 3 of FIG. 2A .
- FIG. 1 shows implantable cardioverter defibrillation (ICD) lead 10 of the present invention.
- ICD lead 10 is used to deliver tip electrode 12 , ring electrode 14 , right ventricle (RV) defibrillation coil 16 and superior vena cava (SVC) defibrillation coil 18 to a heart for the purposes of providing cardio-therapy.
- RV right ventricle
- SVC superior vena cava
- Tip electrode 12 , ring electrode 14 , RV coil 16 and SVC coil 18 are connected at distal end 20 of ICD lead 10 with various conductors that run to proximal end 22 of ICD lead 10 , where the conductors are joined with connector assembly 24 .
- Connector assembly 24 routes the individual conductors to connectors 26 , 28 and 30 for connection with connector sockets of an implantable medical device (IMD).
- IMD implantable medical device
- Tip electrode 12 and ring electrode 14 are connected with connector 28 and with a conductor coil and a conductor cable, respectively, which are electrically isolated within lead 10 .
- Tip electrode 12 and ring electrode 14 are used to sense cardiac signals and to deliver pacing pulses to the right ventricle of the heart in conjunction with the IMD.
- RV coil 16 is joined with connector 26
- SVC coil 18 is joined with connector 30 through conductor cables, which are electrically isolated from each other within in lead 10 .
- RV coil 16 (which is placed in the right ventricle) and SVC coil 18 (which is placed in the superior vena cava) can be used as cathode and anode to deliver defibrillation shocks to the heart from the IMD, as a result of a tachycardia or fibrillation condition sensed in the heart by tip electrode 12 and ring electrode 14 .
- Tip electrode 12 typically comprises a fixation device, such as a helix or corkscrew, which is used to secure tip electrode 12 to tissue of the right ventricular apex of the heart.
- a fixation helix comprises a rigid coil with a sharpened tip that can penetrate into the tissue in order to anchor the position of tip electrode 12 within the heart.
- a rotational force is applied to a torque coil, which then transmits the torque to its distal end and the fixation helix, whereby it attaches to the heart tissue.
- FIG. 2A shows cross section 2 - 2 of FIG. 1 showing the conductors of lead 10 , including coil conductor 34 , sense conductor 36 , RV conductor 38 and SVC conductor 40 .
- FIG. 2B shows a partially cut away perspective view of cross section 2 - 2 of FIG. 1 , in which the features of lead 10 are illustrated. FIGS. 2A and 2B are discussed concurrently.
- ICD lead 10 includes multi-lumen lead body 42 , which includes four lumens 42 A- 42 D for conveying each of the four conductors of lead 10 .
- Lead body 42 is typically comprised of extruded silicone rubber, and is covered by sheathing 44 that protects the components of lead 10 from the environment of the body in which it is implanted.
- Sheathing 44 is also comprised of extruded silicone rubber or another bio-compatible material.
- the conductors used in conjunction with tip electrodes it is desirable for conductors used in conjunction with tip electrodes to have a total inductance in the range of about 1.0 ⁇ H to about 5.0 ⁇ H, preferably greater than about 1.5 ⁇ H.
- a large inductance is necessary due to the relative small surface area of tip electrodes, typically about 2.5 mm 2 ( ⁇ 0.003875 in 2 ) to about 5 mm 2 ( ⁇ 0.00775 in 2 ).
- the inductance of the conductor can be as low as approximately 0.5 ⁇ H, but is preferably higher.
- the inductance of a conductor is determined by its geometric properties, particularly if it is wound into a coil or straight.
- Straight wires have an inductance that approaches zero, and are therefore generally undesirable for small electrodes of leads that have the possibility of exposure to MRI.
- a conductor that includes straight filars in addition to wound filars also has an inductance that approaches zero.
- the inductance of a wound coil is determined by several factors: the diameter of each wire conductor, the pitch of the coil (the distance between turns of the coil), the cross-sectional area occupied by the coil, and the number of filars comprising the coil. These parameters are constrained by the design requirements for each application in which the lead will be used. For example, a typical ICD lead must have an overall diameter less than approximately 6.6 French ( ⁇ 0.0866′′ or ⁇ 0.2198 cm).
- RV conductor 38 comprises a stranded cable conductor in which nineteen wire filars 46 are wrapped around central wire filar 48 inside sheathing 50 .
- SVC conductor 40 comprises a stranded cable conductor in which nineteen wire filars 52 are wrapped around central wire filar 54 inside sheathing 56 .
- the inductance of straight, central filars 48 and 52 effectively reduces the inductance of conductors 38 and 40 to zero.
- RV conductor 38 and SVC conductor 40 are connected with RV coil 16 and SVC coil 18 , which have large enough surface areas, excitation heating is not a concern and neither is the inductance of conductors 38 and 40 .
- Coil conductor 34 is connected with tip electrode 12 , which has a relatively small surface area and is thus susceptible to excitation heating. Therefore, it is important for coil conductor 34 to have a high enough inductance to be RF field compatible. High inductance of coil conductor 34 must be achieved while also maintaining the torque transmitting capabilities of conductor coil 34 . Therefore, the inductance of coil conductor 34 is increased, while maintaining the torque transmitting properties of the coil, utilizing an improved design, the details of which are described in the above referenced co-pending application by Marshall and Schroder.
- Coil conductor 34 is comprised of co-radially wound filars 68 and 70 , that are enveloped in compression sheathing 72 .
- the inductance of coil conductor 34 is increased by reducing the number of filars in the coil.
- the pitch of coil conductor 34 can also be decreased to increase the inductance.
- compression sheathing 72 is extruded around coil conductor 34 in order to restrict radial expansion of the coil when it is placed under torque, thereby increasing its ability to transmit torque from its proximal to distal ends.
- conductor 36 is connected with ring electrode 14 , which has a relatively small surface area for electrodes and is thus susceptible to excitation heating. Therefore, it is important for coil conductor 34 to have a high enough inductance to be RF field compatible. High inductance of conductor 36 must be achieved, however, while also maintaining a conductor that can produce crimps and welds of suitable strength.
- Conductor 34 comprises a multi-filar coil conductor, which is wrapped around a central non-conducting core to form a “coible.” The inductance of sense conductor 36 is improved by replacing the low-inductance and conducting straight filar of previous designs with the non-conducting core.
- FIG. 3 shows cross-section 3 - 3 of FIG. 2A , illustrating a longitudinal cross-section of lead 10 and the winding of conductor 36 .
- Lead 10 includes coil conductor 34 and conductor 36 , which are interposed in multi-lumen lead body 42 and wrapped in sheathing 44 .
- Coil conductor 34 includes conductor filars 68 and 70 , which are wrapped in compression sheathing 72 , which also acts as an insulator and as a protective barrier.
- Coil conductor 36 is connected with tip electrode 12 at its distal end and with connector 28 at its proximal end and is used to deliver pacing stimulus to the heart.
- Conductor 36 includes conductor filars 60 , 62 and 64 , which are wound around core 58 and encased in sheathing 66 .
- Filars 60 , 62 and 64 are form a circuit with ring electrode 14 at their distal end and with connector 28 at their proximal end, and are used in conjunction with coil conductor 34 to perform typical sensing and pacing operations.
- filars 60 , 62 and 64 are uninsulated from each other and form a single circuit with ring electrode 14 and connector 28 .
- more or less filars are used for conductor 36 .
- only two conductor filars are used to further increase the inductance for leads used with tip electrodes, where the electrode surface area is small.
- Conductor 36 has an inner diameter ID, which approximately matches the outer diameter of core 58 .
- Filars 60 , 62 and 64 of conductor 36 are wound to have pitch p.
- the pitch p of coil conductor 36 is selected to produce a high enough inductance in coil conductor 36 to be RF field compatible, given the number of filars chosen for the particular design. In one embodiment, pitch p remains constant from near the proximal end to near the distal end of conductor 36 . In the three-filar embodiment shown in FIG.
- filars 60 , 62 and 64 are comprised of 0.0018′′ ( ⁇ 0.0457 mm) diameter cobalt based sheath, silver core wire such as MP35N®, wound over a 0.007′′ ( ⁇ 0.1778 mm) diameter core and having a pitch of approximately 0.007′′ ( ⁇ 0.1778 mm).
- This configuration yields a conductor with an inductance of approximately 1.0 ⁇ H, which is suitable for use with ring electrodes having a surface area of about 20.0 mm 2 ( ⁇ 0.0310 in 2 ).
- similar wire materials can be used, such as Tantalum sheathings, or silver or gold cores.
- conductor 36 is comprised of 0.0012′′ ( ⁇ 0.0305 mm) diameter MP35N wire wound over a 0.005′′ ( ⁇ 0.127 mm) diameter core at a pitch of 0.006′′ ( ⁇ 0.1524 mm).
- This configuration also yields a conductor with an inductance of approximately 1.0 ⁇ H, which is also suitable for use with ring electrodes.
- a two-filar design includes 0.004′′ ( ⁇ 0.1016 mm) diameter MP35N® wire wound over an approximately 0.018′′ ( ⁇ 0.4572 mm) diameter core at a pitch of approximately 0.010′′ ( ⁇ 0.254 mm).
- This configuration yields a conductor with an inductance of approximately 2.5 ⁇ H, which is suitable for use with electrodes having small surface areas, such as tip electrodes with a 2.5 mm 2 ( ⁇ 0.003875 in 2 ) or greater surface area.
- a four-filar design includes 0.001′′ ( ⁇ 0.0 mm) diameter filars wound over a 0.0055′′ core at a pitch of 0.006′′ ( ⁇ 0.0 mm). This yields a conductor with an inductance of approximately 0.5 mH, which is more suitable for use with electrodes having larger surface areas, such as ring electrodes.
- Inner diameter ID approximately matches the outer diameter of non-conducting core 58 since filars 60 , 62 and 64 are wrapped directly around core 58 .
- filars 60 , 62 and 64 are wrapped tightly around core 58 , but not so tight as to constrict or compress core 58 or to significantly reduce the flexibility of core 58 .
- Core 58 is selected to be of a material having good mechanical properties and is non-conducting. Core 58 must be non-conducting so that it does not affect the inductance of conductor 36 . Core 58 must have good strength so that ring electrode 14 can be properly crimped with conductors 60 , 62 and 64 , such that a sound electrical and mechanical connection is formed.
- Core 58 also provides tensile strength to conductor 36 when electrodes are connected with it. Also, core 58 must be able to withstand elevated temperatures produced during heat treatment of conductor 36 . Core 58 must also have suitable flexibility for implantation and utilization of medical electrical lead 10 .
- Core 58 is comprised of a twisted multi-strand fiber, such as a liquid crystal polymer.
- core 58 is comprised of expanded Teflon® (ePTFE).
- ePTFE expanded Teflon®
- core 58 is comprised of other materials that achieve the above mentioned properties and can have various constructions, such as solid, stranded or particle.
- Conductor 36 is wrapped in sheathing 66 , which is comprised of silicone rubber or another bio-compatible material, such as Ethylene Tetrafluoroethylene (ETFE).
- Ethylene Tetrafluoroethylene Ethylene Tetrafluoroethylene
- the thickness of the jacket is determined by the overall diameter of lead 10 and in one embodiment is 0.00115′′ ( ⁇ 0.0 mm) thick.
- Sheathing 66 serves as an insulating and protective barrier around conductor 36 .
Abstract
Description
- The following co-pending application is filed on the same day as this application: “POLYMER REINFORCED COIL CONDUCTOR FOR TORQUE TRANSMISSION” by inventors M. T. Marshall and H. D. Schroder (attorney docket number P21933), and is incorporated herein by reference.
- The present invention relates generally to implantable medical device (IMD) leads for delivering active electrodes to various places in a human body, such as the heart. In particular, the present invention relates to lead conductors that are compatible with radio frequency (RF) fields generated by magnetic resonance imaging (MRI).
- Typical leads for use with an IMD, such as an implantable cardioverter defibrillation (ICD) device, deliver multiple conductors to the heart for performing pacing, cardioverting, defibrillating, sensing and monitoring functions. One or more of these conductors typically comprises a multi-filar cable in which nineteen filars are wrapped around a straight central filar. This type of design yields a cable that has good mechanical properties, including flexibility, weldability and high strength. Strength is particularly important for ensuring adequate electrical and mechanical contact between the conductor and an electrode when an electrode is crimped down on the conductor. For example, a good crimp should produce a 2.5 lbf joint. These multi-filar, cables, however, have very low inductance particularly due to the straight central filar. During magnetic resonance imaging, it is necessary to expose the patient and the IMD to a radio-frequency field, which is used to generate the MRI image. Generally, it is desirable for a lead conductor to have increased inductance in order to minimize excitation effects from RF fields generated during magnetic resonance imaging.
- The present invention comprises a strength-enhanced conductor for a medical electrical lead. The conductor connects an electrode near a distal end of a medical electrical lead with an implantable medical device connected to a proximal end of the medical electrical lead, and includes a multi-filar coil wrapped around a non-conducting central core. The multi-filar coil includes an inductance of approximately 0.5 μH or greater.
-
FIG. 1 shows a medical electrical lead of the present invention for use with an implantable cardioverter defibrillation (ICD) device. -
FIG. 2A shows cross section 2-2 ofFIG. 1 showing the conductors of the ICD lead. -
FIG. 2B shows a partially cut away perspective view of cross section 2-2 ofFIG. 1 . -
FIG. 3 shows cross section 3-3 ofFIG. 2A . -
FIG. 1 shows implantable cardioverter defibrillation (ICD)lead 10 of the present invention. ICDlead 10 is used to delivertip electrode 12,ring electrode 14, right ventricle (RV)defibrillation coil 16 and superior vena cava (SVC)defibrillation coil 18 to a heart for the purposes of providing cardio-therapy. -
Tip electrode 12,ring electrode 14,RV coil 16 andSVC coil 18 are connected atdistal end 20 ofICD lead 10 with various conductors that run toproximal end 22 ofICD lead 10, where the conductors are joined withconnector assembly 24.Connector assembly 24 routes the individual conductors toconnectors -
Tip electrode 12 andring electrode 14 are connected withconnector 28 and with a conductor coil and a conductor cable, respectively, which are electrically isolated withinlead 10.Tip electrode 12 andring electrode 14 are used to sense cardiac signals and to deliver pacing pulses to the right ventricle of the heart in conjunction with the IMD.RV coil 16 is joined withconnector 26, andSVC coil 18 is joined withconnector 30 through conductor cables, which are electrically isolated from each other within inlead 10. RV coil 16 (which is placed in the right ventricle) and SVC coil 18 (which is placed in the superior vena cava) can be used as cathode and anode to deliver defibrillation shocks to the heart from the IMD, as a result of a tachycardia or fibrillation condition sensed in the heart bytip electrode 12 andring electrode 14. -
Tip electrode 12 typically comprises a fixation device, such as a helix or corkscrew, which is used to securetip electrode 12 to tissue of the right ventricular apex of the heart. A fixation helix comprises a rigid coil with a sharpened tip that can penetrate into the tissue in order to anchor the position oftip electrode 12 within the heart. At the proximal end oflead 10, a rotational force is applied to a torque coil, which then transmits the torque to its distal end and the fixation helix, whereby it attaches to the heart tissue. -
FIG. 2A shows cross section 2-2 ofFIG. 1 showing the conductors oflead 10, includingcoil conductor 34,sense conductor 36,RV conductor 38 andSVC conductor 40.FIG. 2B shows a partially cut away perspective view of cross section 2-2 ofFIG. 1 , in which the features oflead 10 are illustrated.FIGS. 2A and 2B are discussed concurrently. - ICD
lead 10 includesmulti-lumen lead body 42, which includes fourlumens 42A-42D for conveying each of the four conductors oflead 10.Lead body 42 is typically comprised of extruded silicone rubber, and is covered bysheathing 44 that protects the components oflead 10 from the environment of the body in which it is implanted. Sheathing 44 is also comprised of extruded silicone rubber or another bio-compatible material. - As discussed above, exposure of IMD leads to MRI can result in localized heating of electrodes due to excitation of conductors from RF fields used in obtaining MRI images. When an electrode with a small surface area is vibrated by a conductor, excessive heat can build up in the electrode. High levels of vibration in an electrode are correlated with low inductance of the conductor to which it is connected. Conductors with high inductance are more resistant to excitation in RF fields, and are therefore more RF field compatible. For small electrodes, it is desirable to connect them with the IMD using conductors having a large inductance.
- Generally, it is desirable for conductors used in conjunction with tip electrodes to have a total inductance in the range of about 1.0 μH to about 5.0 μH, preferably greater than about 1.5 μH. A large inductance is necessary due to the relative small surface area of tip electrodes, typically about 2.5 mm2 (˜0.003875 in2) to about 5 mm2 (˜0.00775 in2). For ring electrodes, which have surface areas in the range of about 20 mm2 (˜0.0310 in2), the inductance of the conductor can be as low as approximately 0.5 μH, but is preferably higher.
- The inductance of a conductor is determined by its geometric properties, particularly if it is wound into a coil or straight. Straight wires have an inductance that approaches zero, and are therefore generally undesirable for small electrodes of leads that have the possibility of exposure to MRI. A conductor that includes straight filars in addition to wound filars also has an inductance that approaches zero.
- The inductance of a wound coil is determined by several factors: the diameter of each wire conductor, the pitch of the coil (the distance between turns of the coil), the cross-sectional area occupied by the coil, and the number of filars comprising the coil. These parameters are constrained by the design requirements for each application in which the lead will be used. For example, a typical ICD lead must have an overall diameter less than approximately 6.6 French (˜0.0866″ or ˜0.2198 cm).
-
RV conductor 38 comprises a stranded cable conductor in which nineteenwire filars 46 are wrapped aroundcentral wire filar 48 inside sheathing 50. Similarly,SVC conductor 40 comprises a stranded cable conductor in which nineteenwire filars 52 are wrapped aroundcentral wire filar 54 inside sheathing 56. The inductance of straight,central filars conductors RV conductor 38 andSVC conductor 40 are connected withRV coil 16 andSVC coil 18, which have large enough surface areas, excitation heating is not a concern and neither is the inductance ofconductors -
Coil conductor 34 is connected withtip electrode 12, which has a relatively small surface area and is thus susceptible to excitation heating. Therefore, it is important forcoil conductor 34 to have a high enough inductance to be RF field compatible. High inductance ofcoil conductor 34 must be achieved while also maintaining the torque transmitting capabilities ofconductor coil 34. Therefore, the inductance ofcoil conductor 34 is increased, while maintaining the torque transmitting properties of the coil, utilizing an improved design, the details of which are described in the above referenced co-pending application by Marshall and Schroder.Coil conductor 34 is comprised of co-radially wound filars 68 and 70, that are enveloped incompression sheathing 72. In short, the inductance ofcoil conductor 34 is increased by reducing the number of filars in the coil. The pitch ofcoil conductor 34 can also be decreased to increase the inductance. In order to maintain the torque transmitting capabilities ofcoil conductor 34,compression sheathing 72 is extruded aroundcoil conductor 34 in order to restrict radial expansion of the coil when it is placed under torque, thereby increasing its ability to transmit torque from its proximal to distal ends. - Turning to the present invention,
conductor 36 is connected withring electrode 14, which has a relatively small surface area for electrodes and is thus susceptible to excitation heating. Therefore, it is important forcoil conductor 34 to have a high enough inductance to be RF field compatible. High inductance ofconductor 36 must be achieved, however, while also maintaining a conductor that can produce crimps and welds of suitable strength.Conductor 34 comprises a multi-filar coil conductor, which is wrapped around a central non-conducting core to form a “coible.” The inductance ofsense conductor 36 is improved by replacing the low-inductance and conducting straight filar of previous designs with the non-conducting core. This eliminates the inductance of the straight wire filar, which essentially reduces the inductance of the entirety ofconductor 36 to zero. Replacing the nineteen wire filars of previous designs is the multi-filar coil, which is wound around the core in a manner that increases the inductance ofconductor 36. -
FIG. 3 shows cross-section 3-3 ofFIG. 2A , illustrating a longitudinal cross-section oflead 10 and the winding ofconductor 36.Lead 10 includescoil conductor 34 andconductor 36, which are interposed in multi-lumenlead body 42 and wrapped insheathing 44. -
Coil conductor 34 includes conductor filars 68 and 70, which are wrapped incompression sheathing 72, which also acts as an insulator and as a protective barrier.Coil conductor 36 is connected withtip electrode 12 at its distal end and withconnector 28 at its proximal end and is used to deliver pacing stimulus to the heart. -
Conductor 36 includesconductor filars core 58 and encased insheathing 66.Filars ring electrode 14 at their distal end and withconnector 28 at their proximal end, and are used in conjunction withcoil conductor 34 to perform typical sensing and pacing operations. In one embodiment,filars ring electrode 14 andconnector 28. In other embodiments, more or less filars are used forconductor 36. For example, in one embodiment, only two conductor filars are used to further increase the inductance for leads used with tip electrodes, where the electrode surface area is small. -
Conductor 36 has an inner diameter ID, which approximately matches the outer diameter ofcore 58.Filars conductor 36 are wound to have pitch p. The pitch p ofcoil conductor 36 is selected to produce a high enough inductance incoil conductor 36 to be RF field compatible, given the number of filars chosen for the particular design. In one embodiment, pitch p remains constant from near the proximal end to near the distal end ofconductor 36. In the three-filar embodiment shown inFIG. 3 , filars 60, 62 and 64 are comprised of 0.0018″ (˜0.0457 mm) diameter cobalt based sheath, silver core wire such as MP35N®, wound over a 0.007″ (˜0.1778 mm) diameter core and having a pitch of approximately 0.007″ (˜0.1778 mm). This configuration yields a conductor with an inductance of approximately 1.0 μH, which is suitable for use with ring electrodes having a surface area of about 20.0 mm2 (˜0.0310 in2). In other embodiments, similar wire materials can be used, such as Tantalum sheathings, or silver or gold cores. - In another three-filar embodiment,
conductor 36 is comprised of 0.0012″ (˜0.0305 mm) diameter MP35N wire wound over a 0.005″ (˜0.127 mm) diameter core at a pitch of 0.006″ (˜0.1524 mm). This configuration also yields a conductor with an inductance of approximately 1.0 μH, which is also suitable for use with ring electrodes. - In another embodiment, a two-filar design includes 0.004″ (˜0.1016 mm) diameter MP35N® wire wound over an approximately 0.018″ (˜0.4572 mm) diameter core at a pitch of approximately 0.010″ (˜0.254 mm). This configuration yields a conductor with an inductance of approximately 2.5 μH, which is suitable for use with electrodes having small surface areas, such as tip electrodes with a 2.5 mm2 (˜0.003875 in2) or greater surface area.
- In another embodiment, a four-filar design includes 0.001″ (˜0.0 mm) diameter filars wound over a 0.0055″ core at a pitch of 0.006″ (˜0.0 mm). This yields a conductor with an inductance of approximately 0.5 mH, which is more suitable for use with electrodes having larger surface areas, such as ring electrodes.
- Inner diameter ID approximately matches the outer diameter of
non-conducting core 58 sincefilars core 58. In one embodiment,filars core 58, but not so tight as to constrict or compresscore 58 or to significantly reduce the flexibility ofcore 58.Core 58 is selected to be of a material having good mechanical properties and is non-conducting.Core 58 must be non-conducting so that it does not affect the inductance ofconductor 36.Core 58 must have good strength so thatring electrode 14 can be properly crimped withconductors Core 58 also provides tensile strength toconductor 36 when electrodes are connected with it. Also,core 58 must be able to withstand elevated temperatures produced during heat treatment ofconductor 36.Core 58 must also have suitable flexibility for implantation and utilization of medicalelectrical lead 10. -
Core 58 is comprised of a twisted multi-strand fiber, such as a liquid crystal polymer. In another embodiment,core 58 is comprised of expanded Teflon® (ePTFE). In other embodiments,core 58 is comprised of other materials that achieve the above mentioned properties and can have various constructions, such as solid, stranded or particle. -
Conductor 36 is wrapped insheathing 66, which is comprised of silicone rubber or another bio-compatible material, such as Ethylene Tetrafluoroethylene (ETFE). The thickness of the jacket is determined by the overall diameter oflead 10 and in one embodiment is 0.00115″ (˜0.0 mm) thick.Sheathing 66 serves as an insulating and protective barrier aroundconductor 36. - Although the present invention has been described with reference to preferred embodiments, workers skilled in the art will recognize that changes may be made in form and detail without departing from the spirit and scope of the invention.
Claims (20)
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US11/343,655 US9901731B2 (en) | 2006-01-31 | 2006-01-31 | Medical electrical lead having improved inductance |
PCT/US2007/060677 WO2007089988A1 (en) | 2006-01-31 | 2007-01-18 | Medical electrical lead having improved inductance |
EP07710188.9A EP1984069B1 (en) | 2006-01-31 | 2007-01-18 | Medical electrical lead having improved inductance |
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US11/343,655 US9901731B2 (en) | 2006-01-31 | 2006-01-31 | Medical electrical lead having improved inductance |
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US20090149906A1 (en) * | 2007-12-06 | 2009-06-11 | Masoud Ameri | Method and apparatus for disconnecting the tip electrode during mri |
US20090149934A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead with shielding |
US20090149920A1 (en) * | 2007-12-06 | 2009-06-11 | Yingbo Li | Leads with high surface resistance |
US20090149909A1 (en) * | 2007-12-06 | 2009-06-11 | Masoud Ameri | Selectively connecting the tip electrode during therapy for mri shielding |
US20090149933A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US20090204182A1 (en) * | 2008-02-11 | 2009-08-13 | Masoud Ameri | Magnetic core flux canceling of ferrites in mri |
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US20090270956A1 (en) * | 2008-04-25 | 2009-10-29 | Pacesetter, Inc. | Implantable medical lead configured for improved mri safety |
US20100001387A1 (en) * | 2007-03-23 | 2010-01-07 | Fujitsu Limited | Electronic device, electronic apparatus mounted with electronic device, article equipped with electronic device and method of producing electronic device |
US20100010602A1 (en) * | 2006-11-30 | 2010-01-14 | Wedan Steven R | Rf rejecting lead |
US20100049290A1 (en) * | 2008-08-25 | 2010-02-25 | Pacesetter, Inc. | Mri compatible lead |
WO2010042408A1 (en) * | 2008-10-09 | 2010-04-15 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads having rf compatibility and methods of use and manufacture |
US20100106215A1 (en) * | 2008-10-23 | 2010-04-29 | Stubbs Scott R | Systems and methods to detect implantable medical device configuaration changes affecting mri conditional safety |
US20100114275A1 (en) * | 2008-10-30 | 2010-05-06 | Pacesetter, Inc. | Implantable medical lead including winding for improved mri safety |
US20100234929A1 (en) * | 2009-03-12 | 2010-09-16 | Torsten Scheuermann | Thin profile conductor assembly for medical device leads |
WO2010114429A1 (en) * | 2009-03-31 | 2010-10-07 | St. Jude Medical Ab | A medical implantable lead and a method for manufacturing of such a lead |
US20100331936A1 (en) * | 2009-06-26 | 2010-12-30 | Christopher Perrey | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced mri heating |
US20110087302A1 (en) * | 2009-10-09 | 2011-04-14 | Masoud Ameri | Mri compatible medical device lead including transmission line notch filters |
US20110125240A1 (en) * | 2009-11-20 | 2011-05-26 | Pacesetter, Inc. | Biocompatible inductor for implantable lead and method of making same |
US20110160816A1 (en) * | 2009-12-30 | 2011-06-30 | Stubbs Scott R | Apparatus to selectively increase medical device lead inner conductor inductance |
US20110160805A1 (en) * | 2009-12-30 | 2011-06-30 | Blair Erbstoeszer | Implantable electrical lead including a cooling assembly to dissipate mri induced electrode heat |
US20110208280A1 (en) * | 2010-02-19 | 2011-08-25 | Yingbo Li | Lead including conductors configured for reduced mri-induced currents |
US8014867B2 (en) | 2004-12-17 | 2011-09-06 | Cardiac Pacemakers, Inc. | MRI operation modes for implantable medical devices |
US8103360B2 (en) | 2008-05-09 | 2012-01-24 | Foster Arthur J | Medical lead coil conductor with spacer element |
US8160717B2 (en) | 2008-02-19 | 2012-04-17 | Cardiac Pacemakers, Inc. | Model reference identification and cancellation of magnetically-induced voltages in a gradient magnetic field |
US8244346B2 (en) | 2008-02-06 | 2012-08-14 | Cardiac Pacemakers, Inc. | Lead with MRI compatible design features |
US8335572B2 (en) | 2009-10-08 | 2012-12-18 | Cardiac Pacemakers, Inc. | Medical device lead including a flared conductive coil |
US8391994B2 (en) | 2009-12-31 | 2013-03-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion |
US8560084B2 (en) | 2011-08-30 | 2013-10-15 | Greatbatch Ltd. | Lead body with inner and outer co-axial coils |
US8565874B2 (en) | 2009-12-08 | 2013-10-22 | Cardiac Pacemakers, Inc. | Implantable medical device with automatic tachycardia detection and control in MRI environments |
US8571661B2 (en) | 2008-10-02 | 2013-10-29 | Cardiac Pacemakers, Inc. | Implantable medical device responsive to MRI induced capture threshold changes |
US8630718B2 (en) | 2010-11-18 | 2014-01-14 | Cardiac Pacemakers, Inc. | Insulative structure for MRI compatible leads |
US8639331B2 (en) | 2009-02-19 | 2014-01-28 | Cardiac Pacemakers, Inc. | Systems and methods for providing arrhythmia therapy in MRI environments |
US8666511B2 (en) | 2012-07-30 | 2014-03-04 | Medtronic, Inc. | Magnetic resonance imaging compatible medical electrical lead and method of making the same |
US8666512B2 (en) | 2011-11-04 | 2014-03-04 | Cardiac Pacemakers, Inc. | Implantable medical device lead including inner coil reverse-wound relative to shocking coil |
US8798767B2 (en) | 2009-12-31 | 2014-08-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US8825179B2 (en) | 2012-04-20 | 2014-09-02 | Cardiac Pacemakers, Inc. | Implantable medical device lead including a unifilar coiled cable |
US8825181B2 (en) | 2010-08-30 | 2014-09-02 | Cardiac Pacemakers, Inc. | Lead conductor with pitch and torque control for MRI conditionally safe use |
US8897887B2 (en) | 2006-06-08 | 2014-11-25 | Greatbatch Ltd. | Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices |
US8954168B2 (en) | 2012-06-01 | 2015-02-10 | Cardiac Pacemakers, Inc. | Implantable device lead including a distal electrode assembly with a coiled component |
US8958889B2 (en) | 2012-08-31 | 2015-02-17 | Cardiac Pacemakers, Inc. | MRI compatible lead coil |
US8983623B2 (en) | 2012-10-18 | 2015-03-17 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
US9108066B2 (en) | 2008-03-20 | 2015-08-18 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9248283B2 (en) | 2001-04-13 | 2016-02-02 | Greatbatch Ltd. | Band stop filter comprising an inductive component disposed in a lead wire in series with an electrode |
US9254380B2 (en) | 2009-10-19 | 2016-02-09 | Cardiac Pacemakers, Inc. | MRI compatible tachycardia lead |
US9295828B2 (en) | 2001-04-13 | 2016-03-29 | Greatbatch Ltd. | Self-resonant inductor wound portion of an implantable lead for enhanced MRI compatibility of active implantable medical devices |
US9402996B2 (en) | 2014-02-11 | 2016-08-02 | Cardiac Pacemakers, Inc. | RF shield for an implantable lead |
US9427596B2 (en) | 2013-01-16 | 2016-08-30 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9504821B2 (en) | 2014-02-26 | 2016-11-29 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia lead |
US9750944B2 (en) | 2009-12-30 | 2017-09-05 | Cardiac Pacemakers, Inc. | MRI-conditionally safe medical device lead |
USRE46699E1 (en) | 2013-01-16 | 2018-02-06 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9931514B2 (en) | 2013-06-30 | 2018-04-03 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US10080889B2 (en) | 2009-03-19 | 2018-09-25 | Greatbatch Ltd. | Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD |
US20180339882A1 (en) * | 2017-05-23 | 2018-11-29 | Otis Elevator Company | Lightweight elevator traveling cable |
US10350421B2 (en) | 2013-06-30 | 2019-07-16 | Greatbatch Ltd. | Metallurgically bonded gold pocket pad for grounding an EMI filter to a hermetic terminal for an active implantable medical device |
US10559409B2 (en) | 2017-01-06 | 2020-02-11 | Greatbatch Ltd. | Process for manufacturing a leadless feedthrough for an active implantable medical device |
US10561837B2 (en) | 2011-03-01 | 2020-02-18 | Greatbatch Ltd. | Low equivalent series resistance RF filter for an active implantable medical device utilizing a ceramic reinforced metal composite filled via |
US10589107B2 (en) | 2016-11-08 | 2020-03-17 | Greatbatch Ltd. | Circuit board mounted filtered feedthrough assembly having a composite conductive lead for an AIMD |
US10905888B2 (en) | 2018-03-22 | 2021-02-02 | Greatbatch Ltd. | Electrical connection for an AIMD EMI filter utilizing an anisotropic conductive layer |
US10912945B2 (en) | 2018-03-22 | 2021-02-09 | Greatbatch Ltd. | Hermetic terminal for an active implantable medical device having a feedthrough capacitor partially overhanging a ferrule for high effective capacitance area |
US11198014B2 (en) | 2011-03-01 | 2021-12-14 | Greatbatch Ltd. | Hermetically sealed filtered feedthrough assembly having a capacitor with an oxide resistant electrical connection to an active implantable medical device housing |
Families Citing this family (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9037263B2 (en) * | 2008-03-12 | 2015-05-19 | Medtronic, Inc. | System and method for implantable medical device lead shielding |
US9561036B2 (en) * | 2013-09-04 | 2017-02-07 | Rush University Medical Center | Catheter lumen partitioner |
US11742106B2 (en) * | 2021-07-15 | 2023-08-29 | Spr Therapeutics, Inc. | Fracture resistant stimulation lead |
Citations (46)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4135518A (en) * | 1976-05-21 | 1979-01-23 | Medtronic, Inc. | Body implantable lead and electrode |
US4493329A (en) * | 1982-08-19 | 1985-01-15 | Lynn Crawford | Implantable electrode having different stiffening and curvature maintaining characteristics along its length |
US4643202A (en) * | 1985-04-15 | 1987-02-17 | Cordis Corporation | Multi-material insulation sheath for pacer lead |
US5056516A (en) * | 1989-11-02 | 1991-10-15 | Intermedics, Inc. | Implantable endocordial lead with torque-transmitting lanyard |
US5231996A (en) * | 1992-01-28 | 1993-08-03 | Medtronic, Inc. | Removable endocardial lead |
US5276398A (en) * | 1992-06-01 | 1994-01-04 | Conductus, Inc. | Superconducting magnetic resonance probe coil |
US5330522A (en) * | 1992-12-29 | 1994-07-19 | Siemens Pacesetter, Inc. | Ring electrode for a multilumen lead and method of constructing a multilumen lead |
US5387199A (en) * | 1992-02-24 | 1995-02-07 | Baxter International Inc. | Polymer blends for torque transmitting catheters |
US5425755A (en) * | 1992-12-04 | 1995-06-20 | Pacesetter, Inc. | Rotatable pin, screw-in pacing and sensing lead having Teflon-coated conductor coil |
US5456707A (en) * | 1993-10-22 | 1995-10-10 | Vitatron Medical Bv | Pacing lead with improved torsion characteristics |
US5522875A (en) * | 1994-07-28 | 1996-06-04 | Medtronic, Inc. | Medical electrical lead system having a torque transfer stylet |
US5584873A (en) * | 1995-05-08 | 1996-12-17 | Medtronic, Inc. | Medical lead with compression lumens |
US5599576A (en) * | 1995-02-06 | 1997-02-04 | Surface Solutions Laboratories, Inc. | Medical apparatus with scratch-resistant coating and method of making same |
US5935159A (en) * | 1996-12-19 | 1999-08-10 | Medtronic, Inc. | Medical electrical lead |
US5957970A (en) * | 1998-02-18 | 1999-09-28 | Medtronic, Inc. | Method of fabricating a medical electrical lead |
US5968087A (en) * | 1996-12-19 | 1999-10-19 | Medtronic, Inc. | Multi-component lead body for medical electrical leads |
US6078840A (en) * | 1997-04-30 | 2000-06-20 | Medtronic, Inc. | Medical electrical lead having improved fixation |
US6178355B1 (en) * | 1997-04-29 | 2001-01-23 | Medtronic, Inc. | Intracardiac defibrillation leads |
US6249708B1 (en) * | 1997-08-26 | 2001-06-19 | Angeion Corporation | Fluted channel construction for a multi-conductor catheter lead |
US6289250B1 (en) * | 1998-05-27 | 2001-09-11 | Kabushiki Kaisha Cardio-Pacing Research Laboratory | Implantable electrode lead |
US6295476B1 (en) * | 1999-11-01 | 2001-09-25 | Medtronic, Inc. | Medical lead conductor fracture visualization method and apparatus |
US6400992B1 (en) * | 1999-03-18 | 2002-06-04 | Medtronic, Inc. | Co-extruded, multi-lumen medical lead |
US6493591B1 (en) * | 2000-07-19 | 2002-12-10 | Medtronic, Inc. | Implantable active fixation lead with guidewire tip |
US6501994B1 (en) * | 1997-12-24 | 2002-12-31 | Cardiac Pacemakers, Inc. | High impedance electrode tip |
US6501991B1 (en) * | 2000-06-21 | 2002-12-31 | Medtronic, Inc. | Electrically-isolated multiple conductor lead body |
US6516230B2 (en) * | 2000-04-26 | 2003-02-04 | Medtronic, Inc. | Medical electrical lead with fiber core |
US20030083726A1 (en) * | 2001-10-31 | 2003-05-01 | Medtronic, Inc. | Method and apparatus for shunting induced currents in an electrical lead |
US20030144720A1 (en) * | 2002-01-29 | 2003-07-31 | Villaseca Eduardo H. | Electromagnetic trap for a lead |
US20030144718A1 (en) * | 2002-01-29 | 2003-07-31 | Zeijlemaker Volkert A. | Method and apparatus for shielding coating for MRI resistant electrode systems |
US20030144716A1 (en) * | 2002-01-29 | 2003-07-31 | Reinke James D. | Method and apparatus for shunting induced currents in an electrical lead |
US20030144719A1 (en) * | 2002-01-29 | 2003-07-31 | Zeijlemaker Volkert A. | Method and apparatus for shielding wire for MRI resistant electrode systems |
US20040193140A1 (en) * | 2003-03-27 | 2004-09-30 | Scimed Life Systems,Inc. | Medical device |
US6813521B2 (en) * | 2001-04-17 | 2004-11-02 | Medtronic, Inc. | Medical electrical lead |
US20040222658A1 (en) * | 2003-03-24 | 2004-11-11 | Christopher Dilluvio | Retractable roof structural system |
US6825334B1 (en) * | 1998-07-16 | 2004-11-30 | Institut Pasteur | Peptides of IL-2 and derivatives thereof and their use as therapeutic agents |
US20050027342A1 (en) * | 2003-07-30 | 2005-02-03 | Medtronic, Inc. | Multi-lumen medical electrical lead body |
US6854994B2 (en) * | 2001-04-19 | 2005-02-15 | Medtronic, Inc. | Medical electrical lead connector arrangement including anti-rotation means |
US20050055068A1 (en) * | 2000-11-30 | 2005-03-10 | Cardiac Pacemakers, Inc. | Telemetry apparatus and method for an implantable medical device |
US20050197677A1 (en) * | 2004-02-12 | 2005-09-08 | Stevenson Robert A. | Apparatus and process for reducing the susceptability of active implantable medical devices to medical procedures such as magnetic resonance imaging |
US20050222657A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable lead |
US20050222659A1 (en) * | 2004-03-30 | 2005-10-06 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
US20050222656A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable medical device |
US20050246007A1 (en) * | 2004-04-28 | 2005-11-03 | Medtronic, Inc. | Novel lead body assemblies |
US20060041294A1 (en) * | 2004-08-20 | 2006-02-23 | Biophan Technologies, Inc. | Magnetic resonance imaging interference immune device |
US20060229693A1 (en) * | 2005-03-31 | 2006-10-12 | Bauer Ryan T | Medical electrical lead with co-radial multi-conductor coil |
US20060252314A1 (en) * | 2005-05-04 | 2006-11-09 | Ergin Atalar | Electrical lead for an electronic device such as an implantable device |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CH653559A5 (en) | 1980-11-15 | 1986-01-15 | Osypka Peter | Pacemaker electrode |
US6925334B1 (en) | 2003-08-04 | 2005-08-02 | Pacesetter, Inc. | Implantable medical lead having multiple, jointly insulated electrical conductors |
US20050070972A1 (en) | 2003-09-26 | 2005-03-31 | Wahlstrand Carl D. | Energy shunt for producing an MRI-safe implantable medical device |
US7877150B2 (en) | 2004-03-30 | 2011-01-25 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
-
2006
- 2006-01-31 US US11/343,655 patent/US9901731B2/en active Active
-
2007
- 2007-01-18 WO PCT/US2007/060677 patent/WO2007089988A1/en active Application Filing
- 2007-01-18 EP EP07710188.9A patent/EP1984069B1/en active Active
Patent Citations (51)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4135518A (en) * | 1976-05-21 | 1979-01-23 | Medtronic, Inc. | Body implantable lead and electrode |
US4493329A (en) * | 1982-08-19 | 1985-01-15 | Lynn Crawford | Implantable electrode having different stiffening and curvature maintaining characteristics along its length |
US4643202A (en) * | 1985-04-15 | 1987-02-17 | Cordis Corporation | Multi-material insulation sheath for pacer lead |
US5056516A (en) * | 1989-11-02 | 1991-10-15 | Intermedics, Inc. | Implantable endocordial lead with torque-transmitting lanyard |
US5231996A (en) * | 1992-01-28 | 1993-08-03 | Medtronic, Inc. | Removable endocardial lead |
US5387199A (en) * | 1992-02-24 | 1995-02-07 | Baxter International Inc. | Polymer blends for torque transmitting catheters |
US5276398A (en) * | 1992-06-01 | 1994-01-04 | Conductus, Inc. | Superconducting magnetic resonance probe coil |
US5425755A (en) * | 1992-12-04 | 1995-06-20 | Pacesetter, Inc. | Rotatable pin, screw-in pacing and sensing lead having Teflon-coated conductor coil |
US5330522A (en) * | 1992-12-29 | 1994-07-19 | Siemens Pacesetter, Inc. | Ring electrode for a multilumen lead and method of constructing a multilumen lead |
US5456707A (en) * | 1993-10-22 | 1995-10-10 | Vitatron Medical Bv | Pacing lead with improved torsion characteristics |
US5522875A (en) * | 1994-07-28 | 1996-06-04 | Medtronic, Inc. | Medical electrical lead system having a torque transfer stylet |
US5599576A (en) * | 1995-02-06 | 1997-02-04 | Surface Solutions Laboratories, Inc. | Medical apparatus with scratch-resistant coating and method of making same |
US5584873A (en) * | 1995-05-08 | 1996-12-17 | Medtronic, Inc. | Medical lead with compression lumens |
US5935159A (en) * | 1996-12-19 | 1999-08-10 | Medtronic, Inc. | Medical electrical lead |
US5968087A (en) * | 1996-12-19 | 1999-10-19 | Medtronic, Inc. | Multi-component lead body for medical electrical leads |
US6178355B1 (en) * | 1997-04-29 | 2001-01-23 | Medtronic, Inc. | Intracardiac defibrillation leads |
US6078840A (en) * | 1997-04-30 | 2000-06-20 | Medtronic, Inc. | Medical electrical lead having improved fixation |
US6249708B1 (en) * | 1997-08-26 | 2001-06-19 | Angeion Corporation | Fluted channel construction for a multi-conductor catheter lead |
US6501994B1 (en) * | 1997-12-24 | 2002-12-31 | Cardiac Pacemakers, Inc. | High impedance electrode tip |
US5957970A (en) * | 1998-02-18 | 1999-09-28 | Medtronic, Inc. | Method of fabricating a medical electrical lead |
US6289250B1 (en) * | 1998-05-27 | 2001-09-11 | Kabushiki Kaisha Cardio-Pacing Research Laboratory | Implantable electrode lead |
US6825334B1 (en) * | 1998-07-16 | 2004-11-30 | Institut Pasteur | Peptides of IL-2 and derivatives thereof and their use as therapeutic agents |
US6400992B1 (en) * | 1999-03-18 | 2002-06-04 | Medtronic, Inc. | Co-extruded, multi-lumen medical lead |
US6434430B2 (en) * | 1999-03-18 | 2002-08-13 | Medtronic, Inc. | Co-extruded, multi-lumen medical lead |
US6295476B1 (en) * | 1999-11-01 | 2001-09-25 | Medtronic, Inc. | Medical lead conductor fracture visualization method and apparatus |
US6516230B2 (en) * | 2000-04-26 | 2003-02-04 | Medtronic, Inc. | Medical electrical lead with fiber core |
US6501991B1 (en) * | 2000-06-21 | 2002-12-31 | Medtronic, Inc. | Electrically-isolated multiple conductor lead body |
US6493591B1 (en) * | 2000-07-19 | 2002-12-10 | Medtronic, Inc. | Implantable active fixation lead with guidewire tip |
US20050055068A1 (en) * | 2000-11-30 | 2005-03-10 | Cardiac Pacemakers, Inc. | Telemetry apparatus and method for an implantable medical device |
US6813521B2 (en) * | 2001-04-17 | 2004-11-02 | Medtronic, Inc. | Medical electrical lead |
US6854994B2 (en) * | 2001-04-19 | 2005-02-15 | Medtronic, Inc. | Medical electrical lead connector arrangement including anti-rotation means |
US20030083726A1 (en) * | 2001-10-31 | 2003-05-01 | Medtronic, Inc. | Method and apparatus for shunting induced currents in an electrical lead |
US20030144720A1 (en) * | 2002-01-29 | 2003-07-31 | Villaseca Eduardo H. | Electromagnetic trap for a lead |
US20030144718A1 (en) * | 2002-01-29 | 2003-07-31 | Zeijlemaker Volkert A. | Method and apparatus for shielding coating for MRI resistant electrode systems |
US20030144716A1 (en) * | 2002-01-29 | 2003-07-31 | Reinke James D. | Method and apparatus for shunting induced currents in an electrical lead |
US20030144721A1 (en) * | 2002-01-29 | 2003-07-31 | Villaseca Eduardo H. | Conditioning of coupled electromagnetic signals on a lead |
US20030144719A1 (en) * | 2002-01-29 | 2003-07-31 | Zeijlemaker Volkert A. | Method and apparatus for shielding wire for MRI resistant electrode systems |
US7013180B2 (en) * | 2002-01-29 | 2006-03-14 | Medtronic, Inc. | Conditioning of coupled electromagnetic signals on a lead |
US20040222658A1 (en) * | 2003-03-24 | 2004-11-11 | Christopher Dilluvio | Retractable roof structural system |
US20040193140A1 (en) * | 2003-03-27 | 2004-09-30 | Scimed Life Systems,Inc. | Medical device |
US20050027342A1 (en) * | 2003-07-30 | 2005-02-03 | Medtronic, Inc. | Multi-lumen medical electrical lead body |
US7289846B2 (en) * | 2003-07-30 | 2007-10-30 | Medtronic, Inc. | Multi-lumen medical electrical lead body |
US20050197677A1 (en) * | 2004-02-12 | 2005-09-08 | Stevenson Robert A. | Apparatus and process for reducing the susceptability of active implantable medical devices to medical procedures such as magnetic resonance imaging |
US20050222657A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable lead |
US20050222659A1 (en) * | 2004-03-30 | 2005-10-06 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
US20050222656A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable medical device |
US7844343B2 (en) * | 2004-03-30 | 2010-11-30 | Medtronic, Inc. | MRI-safe implantable medical device |
US20050246007A1 (en) * | 2004-04-28 | 2005-11-03 | Medtronic, Inc. | Novel lead body assemblies |
US20060041294A1 (en) * | 2004-08-20 | 2006-02-23 | Biophan Technologies, Inc. | Magnetic resonance imaging interference immune device |
US20060229693A1 (en) * | 2005-03-31 | 2006-10-12 | Bauer Ryan T | Medical electrical lead with co-radial multi-conductor coil |
US20060252314A1 (en) * | 2005-05-04 | 2006-11-09 | Ergin Atalar | Electrical lead for an electronic device such as an implantable device |
Cited By (114)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9295828B2 (en) | 2001-04-13 | 2016-03-29 | Greatbatch Ltd. | Self-resonant inductor wound portion of an implantable lead for enhanced MRI compatibility of active implantable medical devices |
US9248283B2 (en) | 2001-04-13 | 2016-02-02 | Greatbatch Ltd. | Band stop filter comprising an inductive component disposed in a lead wire in series with an electrode |
US8886317B2 (en) | 2004-12-17 | 2014-11-11 | Cardiac Pacemakers, Inc. | MRI operation modes for implantable medical devices |
US8014867B2 (en) | 2004-12-17 | 2011-09-06 | Cardiac Pacemakers, Inc. | MRI operation modes for implantable medical devices |
US8543207B2 (en) | 2004-12-17 | 2013-09-24 | Cardiac Pacemakers, Inc. | MRI operation modes for implantable medical devices |
US8897887B2 (en) | 2006-06-08 | 2014-11-25 | Greatbatch Ltd. | Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices |
US7986999B2 (en) | 2006-11-30 | 2011-07-26 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US8401671B2 (en) | 2006-11-30 | 2013-03-19 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US8170688B2 (en) | 2006-11-30 | 2012-05-01 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US8670840B2 (en) | 2006-11-30 | 2014-03-11 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US20100010602A1 (en) * | 2006-11-30 | 2010-01-14 | Wedan Steven R | Rf rejecting lead |
US20100001387A1 (en) * | 2007-03-23 | 2010-01-07 | Fujitsu Limited | Electronic device, electronic apparatus mounted with electronic device, article equipped with electronic device and method of producing electronic device |
US20090112300A1 (en) * | 2007-10-29 | 2009-04-30 | Horn-Wyffels Mitchell L | Reduced bending stiffness polyurethane tubing |
WO2009058459A1 (en) * | 2007-10-29 | 2009-05-07 | Cardiac Pacemakers, Inc. | Reduced bending stiffness polyurethane tubing |
US8275464B2 (en) | 2007-12-06 | 2012-09-25 | Cardiac Pacemakers, Inc. | Leads with high surface resistance |
US8538551B2 (en) | 2007-12-06 | 2013-09-17 | Cardiac Pacemakers, Inc. | Leads with high surface resistance |
US8731685B2 (en) | 2007-12-06 | 2014-05-20 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US8788058B2 (en) | 2007-12-06 | 2014-07-22 | Cardiac Pacemakers, Inc. | Leads with high surface resistance |
US20090149909A1 (en) * | 2007-12-06 | 2009-06-11 | Masoud Ameri | Selectively connecting the tip electrode during therapy for mri shielding |
US20090149933A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US8666513B2 (en) | 2007-12-06 | 2014-03-04 | Cardiac Pacemakers, Inc. | Implantable lead with shielding |
US8897875B2 (en) | 2007-12-06 | 2014-11-25 | Cardiac Pacemakers, Inc. | Selectively connecting the tip electrode during therapy for MRI shielding |
US8554335B2 (en) | 2007-12-06 | 2013-10-08 | Cardiac Pacemakers, Inc. | Method and apparatus for disconnecting the tip electrode during MRI |
US8086321B2 (en) | 2007-12-06 | 2011-12-27 | Cardiac Pacemakers, Inc. | Selectively connecting the tip electrode during therapy for MRI shielding |
US20090149920A1 (en) * | 2007-12-06 | 2009-06-11 | Yingbo Li | Leads with high surface resistance |
US8032228B2 (en) | 2007-12-06 | 2011-10-04 | Cardiac Pacemakers, Inc. | Method and apparatus for disconnecting the tip electrode during MRI |
US20090149934A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead with shielding |
US20090149906A1 (en) * | 2007-12-06 | 2009-06-11 | Masoud Ameri | Method and apparatus for disconnecting the tip electrode during mri |
US8666508B2 (en) | 2008-02-06 | 2014-03-04 | Cardiac Pacemakers, Inc. | Lead with MRI compatible design features |
US8244346B2 (en) | 2008-02-06 | 2012-08-14 | Cardiac Pacemakers, Inc. | Lead with MRI compatible design features |
US8311637B2 (en) | 2008-02-11 | 2012-11-13 | Cardiac Pacemakers, Inc. | Magnetic core flux canceling of ferrites in MRI |
US8255055B2 (en) | 2008-02-11 | 2012-08-28 | Cardiac Pacemakers, Inc. | MRI shielding in electrodes using AC pacing |
US20090204182A1 (en) * | 2008-02-11 | 2009-08-13 | Masoud Ameri | Magnetic core flux canceling of ferrites in mri |
US20090204171A1 (en) * | 2008-02-11 | 2009-08-13 | Masoud Ameri | Mri shielding in electrodes using ac pacing |
US8160717B2 (en) | 2008-02-19 | 2012-04-17 | Cardiac Pacemakers, Inc. | Model reference identification and cancellation of magnetically-induced voltages in a gradient magnetic field |
US9108066B2 (en) | 2008-03-20 | 2015-08-18 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US20090270956A1 (en) * | 2008-04-25 | 2009-10-29 | Pacesetter, Inc. | Implantable medical lead configured for improved mri safety |
US8103360B2 (en) | 2008-05-09 | 2012-01-24 | Foster Arthur J | Medical lead coil conductor with spacer element |
US8688236B2 (en) | 2008-05-09 | 2014-04-01 | Cardiac Pacemakers, Inc. | Medical lead coil conductor with spacer element |
US20100049290A1 (en) * | 2008-08-25 | 2010-02-25 | Pacesetter, Inc. | Mri compatible lead |
US8244375B2 (en) | 2008-08-25 | 2012-08-14 | Pacesetter, Inc. | MRI compatible lead |
US9561378B2 (en) | 2008-10-02 | 2017-02-07 | Cardiac Pacemakers, Inc. | Implantable medical device responsive to MRI induced capture threshold changes |
US8571661B2 (en) | 2008-10-02 | 2013-10-29 | Cardiac Pacemakers, Inc. | Implantable medical device responsive to MRI induced capture threshold changes |
US20100094364A1 (en) * | 2008-10-09 | 2010-04-15 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads having rf compatibility and methods of use and manufacture |
US8774939B2 (en) | 2008-10-09 | 2014-07-08 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads having RF compatibility and methods of use and manufacture |
US8335570B2 (en) | 2008-10-09 | 2012-12-18 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads having RF compatibility and methods of use and manufacture |
WO2010042408A1 (en) * | 2008-10-09 | 2010-04-15 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads having rf compatibility and methods of use and manufacture |
US20100106215A1 (en) * | 2008-10-23 | 2010-04-29 | Stubbs Scott R | Systems and methods to detect implantable medical device configuaration changes affecting mri conditional safety |
US20100114275A1 (en) * | 2008-10-30 | 2010-05-06 | Pacesetter, Inc. | Implantable medical lead including winding for improved mri safety |
US8977356B2 (en) | 2009-02-19 | 2015-03-10 | Cardiac Pacemakers, Inc. | Systems and methods for providing arrhythmia therapy in MRI environments |
US8639331B2 (en) | 2009-02-19 | 2014-01-28 | Cardiac Pacemakers, Inc. | Systems and methods for providing arrhythmia therapy in MRI environments |
US20100234929A1 (en) * | 2009-03-12 | 2010-09-16 | Torsten Scheuermann | Thin profile conductor assembly for medical device leads |
US9084883B2 (en) | 2009-03-12 | 2015-07-21 | Cardiac Pacemakers, Inc. | Thin profile conductor assembly for medical device leads |
US10080889B2 (en) | 2009-03-19 | 2018-09-25 | Greatbatch Ltd. | Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD |
US8521307B2 (en) | 2009-03-31 | 2013-08-27 | St. Jude Medical Ab | Implantable MRI compatible medical lead |
WO2010114433A1 (en) * | 2009-03-31 | 2010-10-07 | St. Jude Medical Ab | An implantable mri compatible medical lead with a rotatable control member |
WO2010114432A1 (en) * | 2009-03-31 | 2010-10-07 | St. Jude Medical Ab | An implantable mri compatible medical lead |
WO2010114429A1 (en) * | 2009-03-31 | 2010-10-07 | St. Jude Medical Ab | A medical implantable lead and a method for manufacturing of such a lead |
US8332050B2 (en) | 2009-06-26 | 2012-12-11 | Cardiac Pacemakers, Inc. | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating |
US20100331936A1 (en) * | 2009-06-26 | 2010-12-30 | Christopher Perrey | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced mri heating |
US8744600B2 (en) | 2009-06-26 | 2014-06-03 | Cardiac Pacemakers, Inc. | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating |
US8335572B2 (en) | 2009-10-08 | 2012-12-18 | Cardiac Pacemakers, Inc. | Medical device lead including a flared conductive coil |
US20110087302A1 (en) * | 2009-10-09 | 2011-04-14 | Masoud Ameri | Mri compatible medical device lead including transmission line notch filters |
US8369964B2 (en) | 2009-10-09 | 2013-02-05 | Cardiac Pacemakers, Inc. | MRI compatible medical device lead including transmission line notch filters |
US9254380B2 (en) | 2009-10-19 | 2016-02-09 | Cardiac Pacemakers, Inc. | MRI compatible tachycardia lead |
US20110125240A1 (en) * | 2009-11-20 | 2011-05-26 | Pacesetter, Inc. | Biocompatible inductor for implantable lead and method of making same |
US8565874B2 (en) | 2009-12-08 | 2013-10-22 | Cardiac Pacemakers, Inc. | Implantable medical device with automatic tachycardia detection and control in MRI environments |
US9381371B2 (en) | 2009-12-08 | 2016-07-05 | Cardiac Pacemakers, Inc. | Implantable medical device with automatic tachycardia detection and control in MRI environments |
US9750944B2 (en) | 2009-12-30 | 2017-09-05 | Cardiac Pacemakers, Inc. | MRI-conditionally safe medical device lead |
US8306630B2 (en) | 2009-12-30 | 2012-11-06 | Cardiac Pacemakers, Inc. | Apparatus to selectively increase medical device lead inner conductor inductance |
US20110160805A1 (en) * | 2009-12-30 | 2011-06-30 | Blair Erbstoeszer | Implantable electrical lead including a cooling assembly to dissipate mri induced electrode heat |
US20110160816A1 (en) * | 2009-12-30 | 2011-06-30 | Stubbs Scott R | Apparatus to selectively increase medical device lead inner conductor inductance |
US8406895B2 (en) | 2009-12-30 | 2013-03-26 | Cardiac Pacemakers, Inc. | Implantable electrical lead including a cooling assembly to dissipate MRI induced electrode heat |
US8798767B2 (en) | 2009-12-31 | 2014-08-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US8676351B2 (en) | 2009-12-31 | 2014-03-18 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion |
US9199077B2 (en) | 2009-12-31 | 2015-12-01 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US9050457B2 (en) | 2009-12-31 | 2015-06-09 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile conductor for longitudinal expansion |
US8391994B2 (en) | 2009-12-31 | 2013-03-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion |
US20110208280A1 (en) * | 2010-02-19 | 2011-08-25 | Yingbo Li | Lead including conductors configured for reduced mri-induced currents |
US8498719B2 (en) | 2010-02-19 | 2013-07-30 | Cardiac Pacemakers, Inc. | Lead including conductors configured for reduced MRI-induced currents |
WO2011103444A1 (en) * | 2010-02-19 | 2011-08-25 | Cardiac Pacemakers, Inc. | Lead including conductors configured for reduced mri-induced currents |
US8738150B2 (en) | 2010-02-19 | 2014-05-27 | Cardiac Pacemakers, Inc. | Lead including conductors configured for reduced MRI-induced currents |
US8326436B2 (en) | 2010-02-19 | 2012-12-04 | Cardiac Pacemakers, Inc. | Lead including conductors configured for reduced MRI-induced currents |
US8825181B2 (en) | 2010-08-30 | 2014-09-02 | Cardiac Pacemakers, Inc. | Lead conductor with pitch and torque control for MRI conditionally safe use |
US8630718B2 (en) | 2010-11-18 | 2014-01-14 | Cardiac Pacemakers, Inc. | Insulative structure for MRI compatible leads |
US11198014B2 (en) | 2011-03-01 | 2021-12-14 | Greatbatch Ltd. | Hermetically sealed filtered feedthrough assembly having a capacitor with an oxide resistant electrical connection to an active implantable medical device housing |
US11071858B2 (en) | 2011-03-01 | 2021-07-27 | Greatbatch Ltd. | Hermetically sealed filtered feedthrough having platinum sealed directly to the insulator in a via hole |
US10596369B2 (en) | 2011-03-01 | 2020-03-24 | Greatbatch Ltd. | Low equivalent series resistance RF filter for an active implantable medical device |
US10561837B2 (en) | 2011-03-01 | 2020-02-18 | Greatbatch Ltd. | Low equivalent series resistance RF filter for an active implantable medical device utilizing a ceramic reinforced metal composite filled via |
US9002476B2 (en) | 2011-08-30 | 2015-04-07 | Greatbatch Ltd. | Lead body with inner and outer co-axial coils |
US8560084B2 (en) | 2011-08-30 | 2013-10-15 | Greatbatch Ltd. | Lead body with inner and outer co-axial coils |
US8666512B2 (en) | 2011-11-04 | 2014-03-04 | Cardiac Pacemakers, Inc. | Implantable medical device lead including inner coil reverse-wound relative to shocking coil |
US8825179B2 (en) | 2012-04-20 | 2014-09-02 | Cardiac Pacemakers, Inc. | Implantable medical device lead including a unifilar coiled cable |
US8954168B2 (en) | 2012-06-01 | 2015-02-10 | Cardiac Pacemakers, Inc. | Implantable device lead including a distal electrode assembly with a coiled component |
US9333344B2 (en) | 2012-06-01 | 2016-05-10 | Cardiac Pacemakers, Inc. | Implantable device lead including a distal electrode assembly with a coiled component |
US8666511B2 (en) | 2012-07-30 | 2014-03-04 | Medtronic, Inc. | Magnetic resonance imaging compatible medical electrical lead and method of making the same |
US8958889B2 (en) | 2012-08-31 | 2015-02-17 | Cardiac Pacemakers, Inc. | MRI compatible lead coil |
EP3156100A1 (en) * | 2012-08-31 | 2017-04-19 | Cardiac Pacemakers, Inc. | Mri compatible lead coil |
US8983623B2 (en) | 2012-10-18 | 2015-03-17 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
US9504822B2 (en) | 2012-10-18 | 2016-11-29 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
USRE46699E1 (en) | 2013-01-16 | 2018-02-06 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9427596B2 (en) | 2013-01-16 | 2016-08-30 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9931514B2 (en) | 2013-06-30 | 2018-04-03 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US10350421B2 (en) | 2013-06-30 | 2019-07-16 | Greatbatch Ltd. | Metallurgically bonded gold pocket pad for grounding an EMI filter to a hermetic terminal for an active implantable medical device |
US9402996B2 (en) | 2014-02-11 | 2016-08-02 | Cardiac Pacemakers, Inc. | RF shield for an implantable lead |
US9504821B2 (en) | 2014-02-26 | 2016-11-29 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia lead |
US9682231B2 (en) | 2014-02-26 | 2017-06-20 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia lead |
US10589107B2 (en) | 2016-11-08 | 2020-03-17 | Greatbatch Ltd. | Circuit board mounted filtered feedthrough assembly having a composite conductive lead for an AIMD |
US10559409B2 (en) | 2017-01-06 | 2020-02-11 | Greatbatch Ltd. | Process for manufacturing a leadless feedthrough for an active implantable medical device |
US10556776B2 (en) * | 2017-05-23 | 2020-02-11 | Otis Elevator Company | Lightweight elevator traveling cable |
US20180339882A1 (en) * | 2017-05-23 | 2018-11-29 | Otis Elevator Company | Lightweight elevator traveling cable |
US10912945B2 (en) | 2018-03-22 | 2021-02-09 | Greatbatch Ltd. | Hermetic terminal for an active implantable medical device having a feedthrough capacitor partially overhanging a ferrule for high effective capacitance area |
US10905888B2 (en) | 2018-03-22 | 2021-02-02 | Greatbatch Ltd. | Electrical connection for an AIMD EMI filter utilizing an anisotropic conductive layer |
US11712571B2 (en) | 2018-03-22 | 2023-08-01 | Greatbatch Ltd. | Electrical connection for a hermetic terminal for an active implantable medical device utilizing a ferrule pocket |
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EP1984069B1 (en) | 2014-12-17 |
WO2007089988A1 (en) | 2007-08-09 |
US9901731B2 (en) | 2018-02-27 |
EP1984069A1 (en) | 2008-10-29 |
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